U.S. patent number 8,053,244 [Application Number 12/190,687] was granted by the patent office on 2011-11-08 for magnetic oscillator based biosensor.
This patent grant is currently assigned to Seagate Technology LLC. Invention is credited to Insik Jin, Pat J. Ryan, Haiwen Xi.
United States Patent |
8,053,244 |
Ryan , et al. |
November 8, 2011 |
Magnetic oscillator based biosensor
Abstract
A biosensor is described. The biosensor includes a fixed
multilayer stack providing a magnetization oscillation, a voltage
source electrically coupled to the fixed multilayer stack, and a
binding molecule covalently bonded to the biosensor. The voltage
source provides a direct current through the fixed multilayer stack
to generate the magnetization oscillation and a target molecule
including a magnetic nanoparticle forms a complex with the binding
molecule and alters the magnetization oscillation.
Inventors: |
Ryan; Pat J. (St. Paul, MN),
Xi; Haiwen (Prior Lake, MN), Jin; Insik (Eagan, MN) |
Assignee: |
Seagate Technology LLC (Scotts
Valley, CA)
|
Family
ID: |
41680880 |
Appl.
No.: |
12/190,687 |
Filed: |
August 13, 2008 |
Prior Publication Data
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|
|
|
Document
Identifier |
Publication Date |
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US 20100039105 A1 |
Feb 18, 2010 |
|
Current U.S.
Class: |
436/149; 435/7.1;
324/226; 422/82.01; 436/526; 436/518; 436/524; 436/501; 324/236;
324/228 |
Current CPC
Class: |
G01N
27/745 (20130101) |
Current International
Class: |
G01N
27/00 (20060101); G01N 27/72 (20060101); G01N
33/543 (20060101); G01N 33/551 (20060101) |
Field of
Search: |
;436/94,149,150,501,518,524,526 ;435/6,7.1 ;422/82.01
;324/226,228,236 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Other References
Wang et al., "Towards a Magnetic Microarray for Sensitive
Diagnostics", Journal of Magnetism and Magnetic Materials 293
(2005) 731-739. cited by other .
Han et al., "CMOS Integrated DNA Microarray Based on GMR Sensors",
2006 IEEE. cited by other .
Han et al., "A High-Density Magnetoresistive Biosensor Array with
Drift-Compensation Mechanism", 2007 IEEE International Solid-State
Circuits Conference. cited by other .
Xi et al., "Circular Domain Wall Motion Driven by Spin-Polarized
Currents in Confined Square Nanomagnets", Journal of Applied
Physics 97, 044306 (2005). cited by other .
Kiselev et al., "Microwave Oscillations of a Nanomagnet Drive by a
Spin-Polarized Current", 2003 Nature Publishing Group. cited by
other .
J. Grollier, "Synchronization of Spin-Transfer Oscillators Driven
by Stimulated Microwave Currents", Physical Review B 73, 060409(R)
(2006). cited by other .
Kaka et al., "Mutual Phase-Locking of Microwave Spin Torque
Nano-Oscillators", 2005 Nature Publishing Group. cited by
other.
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Primary Examiner: Wallenhorst; Maureen
Attorney, Agent or Firm: Campbell Nelson Whipps LLC
Claims
What is claimed is:
1. A biosensor, comprising: a multilayer magnetic stack providing a
rotating magnetic field; a voltage source electrically coupled to
the multilayer stack, the voltage source providing a direct current
through the multilayer magnetic stack to generate the rotating
magnetic field with a spin polarized current; a binding molecule
bonded to the multilayer magnetic stack, wherein a target molecule
comprises a magnetic nanoparticle that forms a complex with the
binding molecule and alters the rotating magnetic field.
2. A biosensor according to claim 1, wherein the direct current is
the spin polarized current.
3. A biosensor according to claim 1, wherein the multilayer
magnetic stack spin polarizes direct current and generates the
rotating magnetic field.
4. A biosensor according to claim 1, wherein the multilayer
magnetic stack comprises a non-magnetic barrier layer between a
first magnetic layer and a second magnetic layer, the first
magnetic layer having a first pinned magnetization orientation and
the second magnetic layer having a second free magnetization
orientation that is orthogonal to the first magnetization
orientation.
5. A biosensor according to claim 1, wherein the multilayer
magnetic stack comprises a non-magnetic barrier layer between a
first magnetic layer and a second magnetic layer, the first
magnetic layer having a first pinned magnetization orientation
plane and the second magnetic layer having a second free
magnetization orientation plane that is parallel to the first
magnetization orientation plane.
6. A biosensor according to claim 1, wherein the target molecule is
covalently bonded to the multilayer magnetic stack.
7. A biosensor according to claim 1, further comprising a second
multilayer magnetic stack electrically coupled to the voltage
source and the multilayer magnetic stack in parallel.
8. A biosensor according to claim 1, further comprising a second
multilayer magnetic stack electrically coupled to the voltage
source and the multilayer magnetic stack in series.
9. A biosensor according to claim 1, wherein the voltage source
further comprises an alternating current voltage source.
10. A biosensor according to claim 1, wherein the multilayer
magnetic stack is electrically between a first electrode and a
second electrode, the first electrode and the second electrode
providing an electrical path for the direct current.
11. A biosensor array comprising: a plurality of detection sites
disposed on a substrate; and a voltage source electrically coupled
to the detection sites, the voltage source providing a direct
current to the detection sites; wherein at least selected detection
sites comprise: a multilayer magnetic stack generating a rotating
magnetic field upon passing a spin polarized direct current through
the multilayer magnetic stack; and a binding molecule covalently
bonded to the multilayer magnetic stack, wherein a target molecule
comprises a magnetic nanoparticle that forms a complex with the
binding molecule and alters the rotating magnetic field.
12. A biosensor array according to claim 11, wherein the plurality
of detection sites is subdivided into sub-arrays and at least
selected sub-arrays have different types of binding molecules.
13. A biosensor array according to claim 11, wherein the plurality
of detection sites is subdivided into sub-arrays and at least
selected sub-arrays have different oscillation frequencies.
14. A biosensor array according to claim 11, wherein the multilayer
magnetic stack spin polarizes direct current and generates the
rotating magnetic field.
15. A biosensor array according to claim 11, further comprising a
second multilayer magnetic stack electrically coupled to the
voltage source, and the multilayer magnetic stack is in parallel
connection with the second multilayer magnetic stack.
16. A biosensor array according to claim 11, further comprising a
second multilayer magnetic stack electrically coupled to the
voltage source, and the multilayer magnetic stack is in serial
connection with the second multilayer magnetic stack.
17. A biosensor array according to claim 11, wherein the voltage
source further comprises an alternating current voltage source.
18. A method of detecting a magnetic complex in a sample,
comprising steps of: passing a spin polarized direct current
through a multilayer magnetic stack; generating a rotating magnetic
field in the multilayer magnetic stack with the spin polarized
direct current; detecting the rotating magnetic field; forming a
magnetic complex between a target molecule, comprising a magnetic
nanoparticle located in a sample, and a binding molecule covalently
bonded to the multilayer magnetic stack; and detecting if the
rotating magnetic field has been altered with the magnetic complex
to form an altered rotating magnetic field to determine the
presence of the target molecule in the sample.
19. A method according to claim 18, wherein the multilayer magnetic
stack comprises a non-magnetic barrier layer between a first
magnetic layer and a second magnetic layer, the first magnetic
layer having a first pinned magnetization orientation and the
second magnetic layer having a second free magnetization
orientation that is orthogonal to the first magnetization
orientation and the multilayer magnetic stack spin polarizes direct
current and generates the rotating magnetic field.
20. A method according to claim 18, wherein the multilayer magnetic
stack comprises a non-magnetic barrier layer between a first
magnetic layer and a second magnetic layer, the first magnetic
layer having a first pinned magnetization orientation plane and the
second magnetic layer having a second free magnetization
orientation plane that is parallel to the first magnetization
orientation plane.
Description
BACKGROUND
Biosensing is under current research and development for a wide
range of applications in the field of functional genomics and
molecular diagnostics, for example. One technique uses fluorescent
labels, which are optically detected with laser scanners. However,
the required instrumentation needs to be reduced in size and cost
to realize a hand-held device. Preferred sensing systems have high
sensitivity, rapid response, portability, and low cost, preferably
not requiring DNA amplification process. In addition, the
biosensing system is desired to be compatible with CMOS processing,
and can be easily integrated with a CMOS chip to form a
lab-on-a-chip system.
Biosensing using magnetic microarrays has been proposed. The basic
methodology of such a magnetic microarray is that a single-stranded
DNA with a known sequence is immobilized (bound) on the sensor
surface through a sulfur-Au linkage. Meanwhile, a tagging process
using single-domain high-moment magnetic nanoparticles as tags are
attached to targeted DNA fragments. When the tagged DNA fragments
are selectively captured by complementary DNA probes that are
attached to the sensors, the stray field of the magnetic
nanoparticles is read out by the magnetic sensors. A giant
magnetoresistive spin-valves or magnetic tunnel junction is used
for magnetic field sensing.
One problem with these biosensors is that the sensing suffers from
a large 1/f noise coming from the sensors themselves and from the
MOS switches. There is a need for a biosensor that reduces 1/f
noise without increasing the complexity of the system by
implementing a frequency modulation scheme.
BRIEF SUMMARY
The present disclosure relates to a magnetic oscillator based
biosensor. In particular, the magnetic oscillator based biosensor
can be utilized alone or in a sensor array or biochip. Molecules
such as, for example, DNA or RNA strands are detected by the
oscillation frequency change of the magnetic oscillator based
biosensor by the presence of these molecules tagged with magnetic
nanoparticles. Since the oscillation resides in the GHz regime, the
1/f noise is reduced or avoided.
In an illustrative embodiment, a biosensor includes a fixed
multilayer stack providing a magnetization oscillation, a voltage
source electrically coupled to the fixed multilayer stack, and a
binding molecule covalently bonded to the biosensor. The voltage
source provides a direct current through the fixed multilayer stack
to generate the magnetization oscillation and a target molecule
including a magnetic nanoparticle forms a complex with the binding
molecule and alters the magnetization oscillation.
In another illustrative embodiment, a biosensor array includes a
plurality of detection sites disposed on a substrate and a voltage
source electrically coupled to the detection sites. The voltage
source provides a direct current to the detection sites. At least
selected detection sites include a fixed multilayer stack
generating a magnetization oscillation upon passing a spin
polarized direct current through the fixed multilayer stack, and a
binding molecule covalently bonded to the biosensor. A target
molecule includes a magnetic nanoparticle that forms a complex with
the binding molecule and alters the magnetization oscillation.
An illustrative method of detecting a magnetic complex in a sample
includes the steps of passing a current through a fixed multilayer
stack, generating a magnetization oscillation with the fixed
multilayer stack with the current and detecting the magnetization
oscillation. Then the method includes forming a magnetic complex
with a target molecule. The target molecule includes a magnetic
nanoparticle. A binding molecule is covalently bonded to the
biosensor. Then the method includes detecting if the magnetization
oscillation has been altered with the magnetic complex to form an
altered magnetization oscillation to determine the presence of the
target molecule.
BRIEF DESCRIPTION OF THE DRAWINGS
The disclosure may be more completely understood in consideration
of the following detailed description of various embodiments of the
disclosure in connection with the accompanying drawings, in
which:
FIG. 1 is a schematic diagram of an illustrative biosensor
detecting a target molecule;
FIG. 2 is a schematic circuit diagram of an illustrative magnetic
oscillator;
FIG. 3 is a graph illustrating the magnetization oscillation
frequency as a function of the current flowing through the
exemplary fixed multilayer stack shown in FIG. 2;
FIG. 4 is a schematic diagram of an exemplary fixed multilayer
stack generating a magnetization oscillation;
FIG. 5 is a schematic diagram of another exemplary fixed multilayer
stack generating a magnetization oscillation;
FIG. 6 is a schematic diagram of another exemplary fixed multilayer
stack generating a magnetization oscillation;
FIG. 7 is a schematic circuit diagram of an exemplary fixed
multilayer stack generating a magnetization oscillation;
FIG. 8 is a schematic circuit diagram of another exemplary fixed
multilayer stack generating a magnetization oscillation;
FIG. 9 is a schematic circuit diagram of another exemplary fixed
multilayer stack generating a magnetization oscillation;
FIG. 10 is a schematic block diagram of a magnetic oscillator
biosensor chip architecture; and
FIG. 11 is a flow diagram of an illustrative method for sensing a
target molecule with a magnetic oscillator biosensor.
The figures are not necessarily to scale. Like numbers used in the
figures refer to like components. However, it will be understood
that the use of a number to refer to a component in a given figure
is not intended to limit the component in another figure labeled
with the same number.
DETAILED DESCRIPTION
In the following description, reference is made to the accompanying
set of drawings that form a part hereof and in which are shown by
way of illustration several specific embodiments. It is to be
understood that other embodiments are contemplated and may be made
without departing from the scope or spirit of the present
disclosure. The following detailed description, therefore, is not
to be taken in a limiting sense. The definitions provided herein
are to facilitate understanding of certain terms used frequently
herein and are not meant to limit the scope of the present
disclosure.
Unless otherwise indicated, all numbers expressing feature sizes,
amounts, and physical properties used in the specification and
claims are to be understood as being modified in all instances by
the term "about." Accordingly, unless indicated to the contrary,
the numerical parameters set forth in the foregoing specification
and attached claims are approximations that can vary depending upon
the desired properties sought to be obtained by those skilled in
the art utilizing the teachings disclosed herein.
The recitation of numerical ranges by endpoints includes all
numbers subsumed within that range (e.g. 1 to 5 includes 1, 1.5, 2,
2.75, 3, 3.80, 4, and 5) and any range within that range.
As used in this specification and the appended claims, the singular
forms "a", "an", and "the" encompass embodiments having plural
referents, unless the content clearly dictates otherwise. As used
in this specification and the appended claims, the term "or" is
generally employed in its sense including "and/or" unless the
content clearly dictates otherwise.
A "binding molecule" refers to antibodies, strands of polynucleic
acids (DNA or RNA), and molecular receptors capable of selectively
binding to or `recognizing` potential target molecules such as, for
example, polynucleic acids, enzymes, proteins, peptides,
antibodies, lipids, polymers, metal ions, and low molecular weight
organic and inorganic species such as toxins, drugs (both
prescription and illicit), explosives, and biohazards.
A "target molecule" refers to the molecule, molecular species, or
organism whose presence, absence, or concentration the assay in
question actually determines. Target molecules included include but
are not limited to viruses, bacteria, other biological organisms
such as fungi, antibodies, proteins, peptides, polynucleic acids,
lipids, polymers, pharmaceutical compounds, organic compounds,
biohazardous compounds, explosive compounds, and toxins, among
others.
The present disclosure relates to a magnetic oscillator based
biosensor. In particular, the magnetic oscillator based biosensor
can be utilized alone or in a sensor array or biochip. Molecules
such as, for example, DNA or RNA strands are detected by the
oscillation frequency change of the magnetic oscillator based
biosensor by the presence of these molecules tagged with magnetic
nanoparticles. Since the oscillation resides in the GHz regime, the
1/f noise is reduced or avoided. While the present disclosure is
not so limited, an appreciation of various aspects of the
disclosure will be gained through a discussion of the examples
provided below.
FIG. 1 is a schematic diagram of an illustrative biosensor 10. The
biosensor 10 includes a magnetic field detector 12 and a binding
molecule 13 covalently bonded to the biosensor 10. In many
embodiments, the binding molecule 13 is covalently bonded to the
magnetic field detector 12 or adjacent to the magnetic field
detector 12. A target molecule 14 can be tagged with a magnetic
nanoparticle 15. This tagged target molecule 14 can then be
selectively bound to the binding molecule 13 to form a complex 11.
For example, the binding molecule 13 can be a nucleic acid strand,
and the tagged target molecule 14 can be a nucleic acid strand
having a complementary sequence that hybridizes to a complex 11.
The detector 12 can then interrogate the complex (described below)
to determine the presence, absence, or concentration of the assay
in question.
Useful nanoparticles includes magnetic (i.e., ferromagnetic)
colloidal materials and particles. The magnetic nanoparticles can
be high moment magnetic nanoparticles which are small in size so as
to be superparamagnetic, or synthetic antiferromagnetic
nanoparticles which contain at least two layers of
antiferromagnetically-coupled high moment ferromagnets. Both types
of nanoparticles appear "nonmagnetic" in the absence of magnetic
field, and do not normally agglomerate. In many embodiments,
magnetizable nanoparticles suitable for use include one or more
materials selected from the group consisting of paramagnetic,
superparamagnetic, ferromagnetic, and ferrimagnetic materials, as
well as combinations thereof.
The magnetic nanoparticles preferably possess the following
properties: (1) their remnant magnetization is as small as possible
so that they preferably will not agglomerate in solutions (either
superparamagnetic particles or antiferromagnetic particles can
satisfy this requirement); (2) the tags display high magnetic
moments under a modest magnetic field of about 100 Oe so they can
be readily detected; (3) the size of the tags preferably is
comparable to the target biomolecules so that they do not interfere
with the DNA hybridization process and other biological processes;
(4) the tags preferably are uniform and chemically stable in a
biological environment; and/or (5) the tags preferably are
biocompatible, i.e., water soluble and functionalized so that they
are readily attached to DNA fragments or other biomolecules.
In many embodiments, the nanoparticles are high moment magnetic
nanoparticles such as Co, Fe or CoFe nanocrystals which are
superparamagnetic at room temperature. They can be fabricated by
chemical routes such as salt reduction or compound decomposition in
appropriate solutions. These particles can be synthesized with
controlled size (e.g., 5-12 nm), are monodisperse, and are
stabilized with oleic acid.
Magnetic nanoparticles and nanopowders suitable for use include but
are not limited to Co, Co alloys, ferrites, Cobalt nitride, Cobalt
oxide, Co--Pd, Co--Pt, Iron, Iron alloys, Fe--Au, Fe--Cr, Fe--N,
Fe.sub.3O.sub.4, Fe--Pd, Fe--Pt, Fe--Zr--Nb--B, Mn--N, Nd--Fe--B,
Nd--Fe--B--Nb--Cu, Ni, and Ni alloys. Alternatively and equally
acceptable, a thin layer of gold can be plated onto a magnetic
core, or a poly-L-lysine coated glass surface can be attached to a
magnetic core. Some suitable nanoparticles are commercially
available from, e.g., Nanoprobes, Inc. (Northbrook, Ill.), and
Reade Advanced Materials (Providence, R.I.).
The size of the magnetic nanoparticles suitable for use is
preferably comparable to the size of the target biomolecule to be
worked with, such that the nanoparticles do not interfere with
biological processes such as DNA hybridization. Consequently, the
size of the magnetic nanoparticles can be from about 5 nm to about
250 nm (mean diameter), or from about 5 nm to about 150 nm, or from
about 5 nm to about 20 nm. For example, magnetic nanoparticles
having a mean diameter of 5 nm, 6 nm, 7 nm, 8 nm, 9 nm, 10 nm, 11
mm, 12 nm, 13 nm, 14 nm, 15 nm, 16 nm, 17 nm, 18 nm, 19 nm, 20 nm,
25 nm, 30 nm, 35 nm, 40 nm, 45 nm, 50 nm, 55 nm, 60 nm, 70 nm, 80
nm, 90 nm, 100 nm, 110 nm, 120 nm, 130 nm, 140 nm, and 150 nm, as
well as nanoparticles having mean diameters in ranges between any
two of these values, are suitable for use herein. Further, in
addition to the more common spherical shape of magnetic
nanoparticles, nanoparticles suitable for use with the present
invention can be disks, rods, coils, or fibers.
FIG. 2 is a schematic circuit diagram of an illustrative magnetic
oscillator 50. The magnetic oscillator 50 includes a fixed
multilayer stack that provides a magnetization oscillation. The
fixed multilayer stack can have any useful configuration that
produces a magnetization oscillation. A few embodiments of the
fixed multilayer stack are illustrated in FIGS. 2-9 described
herein. A current passing through the fixed multilayer stack causes
the fixed multilayer stack to generate the magnetization
oscillation. In some embodiments, the fixed multilayer stack has a
magnetic layer with a fixed magnetization to spin polarize direct
current passing through the magnetic layer. In other embodiments, a
spin polarized current passes through the fized multilayer stack.
The spin polarized current exerts a spin torque on a magnetic layer
having a "free" magnetization and excites magnetization
oscillation. In other embodiments, spin polarized current is passed
through the fixed multilayer stack. The spin polarized current
exerts a spin torque on a magnetic layer having a "free"
magnetization and excites magnetization oscillation.
The illustrated magnetic oscillator 50 includes a fixed multilayer
stack including a non-magnetic barrier or spacer layer 56
separating a fixed or pinned magnetic layer 57 and a free magnetic
layer 58. This fixed multilayer stack is electrically between first
electrode 54 and a second electrode 55. The free layer 58 has no or
little coercivity or less magnetic volume, relative to the fixed
layer 57, and its magnetization can be excited by the current, such
as in the form of magnetization rotation/precession or spinwave, at
a frequency that is a function of the current flowing through the
fixed multilayer stack. Current is provided by a voltage source 70.
The current is a direct current. The magnetization oscillation can
be readout at an output 60 in the form of alternating current (AC)
voltage. The fixed or pinned magnetic layer 57 can be either a
single magnetic layer with a large coercivity or a magnetically
soft layer pinned by an antiferromagnetic layer such as, for
example, a synthetic antiferromagnetically coupled structure. The
fixed multilayer stack can be a stack with a metallic spacer, a
current-constrained path spacer, or an oxide barrier. Thus, the
resistance of the fixed multilayer stack can vary in a wide range
to match the impedance of the peripheral circuitry.
When a DC current is driven into the fixed multilayer stack (i.e.,
magnetic pillar), an AC voltage difference with a radio frequency
appears across the stack due to the spin-torque transfer effect,
that means some kind of magnetization precession is excited by the
current in the free layer, which is translated to the AC voltage.
FIG. 3 shows the magnetic field dependence of the oscillation
frequency. With these characteristics, biosensing can be
implemented with the magnetic nano-oscillators as the detector in
FIG. 1. The radio frequency can be generated with and without
magnetic field bias of the nano-oscillators.
FIG. 4 is a schematic circuit diagram of an exemplary fixed
multilayer stack generating a magnetization oscillation. The fixed
multilayer stack 121 includes a nonmagnetic layer 126 separating to
magnetic layers 127, 124. The fixed multilayer stack 121 has a
thickness direction (z-direction), and length (y-direction) and
width (x-direction). A current I (direct current) passes through
the thickness direction (z-direction) of the fixed multilayer stack
121 to generate the varying magnetic field. While the fixed
multilayer stack 121 is illustrated as an elongated cubic form, the
fixed multilayer stack 121 can take any useful shape. In some
embodiments, the magnetization in the z-direction can be achieved
by shape anisotropy associated with greater z-dimension. In some
embodiments, magnetization in the z-direction can be achieved by
magnetic anisotropy that is intrinsic to the material. Electrodes
(not shown) can be in contact with the ends of the fixed multilayer
stack 121 to assist in passing current through the fixed multilayer
stack 121. While the fixed multilayer stack 121 can have any useful
dimension, these structures can be formed on the nanometer
scale.
The nonmagnetic layer 126 is a barrier or spacer layer that has a
thickness less than the spin diffusion length. Thus, spin
polarization of the current I is conserved when it passes through
the nonmagnetic layer 126 into the magnetic layer 124. The
nonmagnetic layer 126 may be made of an insulator material such as
Al.sub.2O.sub.3 or MgO or of a nonmagnetic metal such as Cu. Other
suitable materials may also be used.
The magnetic layers 127, 124 may be made of ferromagnetic (FM)
alloys such as Fe, Co, Ni. The magnetization direction of one
magnetic layer 127 is magnetized (fixed or pinned) in the thickness
or z-direction due to shape anisotropy of this element, while the
magnetization direction of other magnetic layer 124 is free to
rotate under the influence of a spin torque and can be referred to
as a "free layer." The first magnetic layer 127 has its
magnetization orientation fixed or pinned in a direction
perpendicular to the x-y plane of the fixed multilayer stack 121
and the second magnetic layer 124 has its magnetization orientation
(rotatable or free) parallel to the x-y plane of the fixed
multilayer stack 121. Thus, the first magnetic layer 127 has its
magnetization orientation perpendicular to the second magnetic
layer 124 magnetization orientation.
When an electron current is injected into the first magnetic layer
127 in the z-direction, it is spin polarized by the first magnetic
layer 127. The spin polarization of the current I is conserved when
it passes through the nonmagnetic layer 126 into the second
magnetic layer 124. Spin transfer torque arises from the s-d
interaction between the conductive electrons and the local moments
of the magnet. The spin polarized current exerts a torque on the
second magnetic layer 124 magnetization orientation and generates a
magnetization oscillation. In a form of the magnetization
oscillation is the magnetization rotation in the stack plane.
Nevertheless, there is a small component of the magnetization
precession out of the plane, which can be detected as an AC output
voltage.
FIG. 5 is a side view schematic diagram of another exemplary fixed
multilayer stack 122 generating a magnetization oscillation. The
fixed multilayer stack 122 includes a nonmagnetic layer 126
separating to magnetic layers 128, 124. The fixed multilayer stack
122 has a thickness direction (z-direction), and length
(y-direction) and width (x-direction). A spin polarized current I
(direct current) passes through the thickness direction
(z-direction) of the fixed multilayer stack 122 to generate the
magnetization oscillation. While the fixed multilayer stack 122 is
illustrated as a cubic form, the fixed multilayer stack 122 can
take any useful shape. Electrodes (not shown) can be in contact
with the ends of the fixed multilayer stack 122 to assist in
passing the spin polarized current through the fixed multilayer
stack 122. While the fixed multilayer stack 122 can have any useful
dimension, these structures can be formed on the nanometer
scale.
The nonmagnetic layer 126 is a barrier or spacer layer that has a
thickness less than the spin diffusion length. Thus, spin
polarization of the current I is conserved when it passes through
the nonmagnetic layer 126 into the magnetic layer 124. The
nonmagnetic layer 126 may be made of an insulator material such as
Al.sub.2O.sub.3 or MgO or of a nonmagnetic metal such as Cu. Other
suitable materials may also be used.
The magnetic layers 128, 124 may be made of ferromagnetic (FM)
alloys such as Fe, Co, Ni. The magnetization direction of one
magnetic layer 128 is magnetized (fixed or pinned) in the a
direction parallel to the x-y plane of the fixed multilayer stack
122, while the magnetization direction of other magnetic layer 124
is free to rotate under the influence of a spin torque and can be
referred to as a "free layer." The second magnetic layer 124 has
its magnetization orientation (rotatable or free) parallel to the
x-y plane of the fixed multilayer stack 122. Thus, the first
magnetic layer 128 has its magnetization orientation parallel to
the second magnetic layer 124 magnetization orientation.
When a spin polarized electron current I is injected into the fixed
multilayer stack 122 in the z-direction, the spin polarization of
the current I is conserved when it passes through the nonmagnetic
layer 126 into the second magnetic layer 124. Spin transfer torque
arises from the s-d interaction between the conductive electrons
and the local moments of the magnet. The spin polarized current
exerts a torque on the second magnetic layer 124 magnetization
orientation and generates a magnetization oscillation. The
magnetization oscillation can be converted to an AC output voltage
for readout.
FIG. 6 is a side view schematic diagram of another exemplary fixed
multilayer stack 123 generating a magnetization oscillation. The
fixed multilayer stack 123 includes a nonmagnetic layer 126
separating to magnetic layers 128, 124. The fixed multilayer stack
123 has a thickness direction (z-direction), and length
(y-direction) and width (x-direction). A spin polarized current I
(direct current) passes through the thickness direction
(z-direction) of the fixed multilayer stack 123 to generate the
rotating magnetic field. While the fixed multilayer stack 123 is
illustrated as a cubic form, the fixed multilayer stack 123 can
take any useful shape. Electrodes (not shown) can be in contact
with the ends of the fixed multilayer stack 123 to assist in
passing the spin polarized current through the fixed multilayer
stack 23. While the fixed multilayer stack 23 can have any useful
dimension, these structures can be formed on the nanometer
scale.
The nonmagnetic layer 126 is a barrier or spacer layer that has a
thickness less than the spin diffusion length. Thus, spin
polarization of the current I is conserved when it passes through
the nonmagnetic layer 126 into the magnetic layer 124. The
nonmagnetic layer 126 may be made of an insulator material such as
Al.sub.2O.sub.3 or MgO or of a nonmagnetic metal such as Cu. Other
suitable materials may also be used.
The fixed multilayer stack 123 also includes a pinning layer 129.
The pinning layer 129 is an antiferromagnetic layer. The
antiferromagnet has two sublattices of magnetic moments pointing in
opposite directions. When a ferromagnetic layer (i.e., magnetic
layers 128) is in contact with it, the magnetization of the
ferromagnet (i.e., magnetic layers 128) is pinned in a direction.
So the antiferromagnetic layer is called pining layer 129 and the
ferromagnetic layer is called pinned layer 128.
The magnetic layers 128, 124 may be made of ferromagnetic (FM)
alloys such as Fe, Co, Ni. The magnetization direction of one
magnetic layer 128 is magnetized (fixed or pinned) in the a
direction parallel to the x-y plane of the fixed multilayer stack
122, while the magnetization direction of other magnetic layer 124
is free to rotate under the influence of a spin torque and can be
referred to as a "free layer." The second magnetic layer 124 has
its magnetization orientation (rotatable or free) parallel to the
x-y plane of the fixed multilayer stack 122. Thus, the first
magnetic layer 128 has its magnetization orientation parallel to
the second magnetic layer 124 magnetization orientation.
When a spin polarized electron current I is injected into the fixed
multilayer stack 122 in the z-direction, the spin polarization of
the current I is conserved when it passes through the nonmagnetic
layer 126 into the second magnetic layer 124. Spin transfer torque
arises from the s-d interaction between the conductive electrons
and the local moments of the magnet. The spin polarized current
exerts a torque on the second magnetic layer 124 magnetization
orientation and generates a magnetization oscillation. The
magnetization oscillation can be converted into an AC output
voltage for readout.
FIG. 7 is a schematic circuit diagram of another exemplary fixed
multilayer stack generating a rotating magnetic field. The
illustrated magnetic oscillator 51 includes a two fixed multilayer
stacks in parallel electrical connection. The first fixed
multilayer stack includes a non-magnetic barrier or spacer layer 56
separating a fixed or pinned magnetic layer 57 and a free magnetic
layer 158. The second fixed multilayer stack includes a
non-magnetic barrier or spacer layer 156 separating a fixed or
pinned magnetic layer 157 and a free magnetic layer 158. In the
illustrated embodiment the free layer 158 is a co-extensive layer
where the first fixed multilayer stack and the second fixed
multilayer stack share the free layer 158. In some embodiments (not
shown) the pinned layer 55 and 155 can also be a co-extensive layer
where the first fixed multilayer stack and the second fixed
multilayer stack share a common pinned layer. The first fixed
multilayer stack is electrically between a first electrode 54 and a
second electrode 55. The second fixed multilayer stack is
electrically between the first electrode 54 and a third electrode
155.
Current is provided by a voltage source 70. The current is a direct
current. The magnetic rotation frequency can be readout at an
output 60. When a DC current is driven into the fixed multilayer
stack (i.e., magnetic pillar), an AC voltage difference with a
radio frequency appears across the stack due to the spin-torque
transfer effect, that means some kind of magnetization precession
is excited by the current in the free layer, which is translated to
the AC voltage. When DC current is driven into this structure 51
the two fixed multilayer stacks oscillate (i.e., rotate) at a
common frequency with phase lock. A high AC voltage output and
quality factor is achieved. When the two fixed multilayer stacks
are designed to have different magnetic field dependencies of the
each individual oscillation frequency, the phase locking will be
lost in the presence of a magnetic nanoparticle tag magnetic field.
In detection, the common mode of the oscillation between the
nano-oscillators (i.e., fixed multilayer stacks) disappears or
greatly diminishes. Therefore, the detection can be described as a
digital mode in frequency domain.
FIG. 8 is a schematic circuit diagram of another exemplary fixed
multilayer stack generating magnetization oscillation. The
illustrated magnetic oscillator 52 includes a two fixed multilayer
stacks in serial electrical connection. The first fixed multilayer
stack includes a non-magnetic barrier or spacer layer 56 separating
a fixed or pinned magnetic layer 57 and a free magnetic layer 58.
The second fixed multilayer stack includes a non-magnetic barrier
or spacer layer 156 separating a fixed or pinned magnetic layer 157
and a free magnetic layer 158. The first fixed multilayer stack is
electrically between a first electrode 54 and a second electrode
55. The second fixed multilayer stack is electrically between the
third electrode 154 and a fourth electrode 155.
Current is provided by a voltage source 70. The current is a direct
current. The magnetic rotation frequency can be readout at an
output 60. When a DC current is driven into the fixed multilayer
stack (i.e., magnetic pillar), an AC voltage difference with a
radio frequency appears across the stack due to the spin-torque
transfer effect, that means some kind of magnetization precession
is excited by the current in the free layer, which is translated to
the AC voltage. When DC current is driven into this structure 52
the two fixed multilayer stacks oscillate (i.e., rotate) at a
common frequency with phase lock. A high AC voltage output and
quality factor is achieved. When the two fixed multilayer stacks
are designed to have different magnetic field dependencies of the
each individual oscillation frequency, the phase locking will be
lost in the presence of a magnetic nanoparticle tag magnetic field.
In detection, the common mode of the oscillation between the
nano-oscillators (i.e., fixed multilayer stacks) disappears or
greatly diminishes. Therefore, the detection can be described as a
digital mode in frequency domain.
FIG. 9 is a schematic circuit diagram of another exemplary fixed
multilayer stack generating a magnetization oscillation. The
illustrated magnetic oscillator 53 includes two current inputs, a
direct current voltage source 70 and an alternating current voltage
source 170. The fixed multilayer stack includes a non-magnetic
barrier or spacer layer 56 separating a fixed or pinned magnetic
layer 57 and a free magnetic layer 58. The fixed multilayer stack
is electrically between a first electrode 54 and a second electrode
55. The magnetic rotation frequency can be readout at an output
60.
When the intrinsic resonance frequency of the fixed multilayer
stack is close to that of the AC input 170, the oscillation is
locked by the AC current in frequency and phase. Meanwhile, a high
AC voltage output 60 and high quality factor can be achieved. This
design is advantageous since the oscillation can be tuned and
controlled by the AC current in a small frequency range. On the
other hand, the frequency of the AC current can be adjusted
according to the intrinsic resonance frequency of the oscillator.
The detection is same as for those of FIGS. 8 and 9. Presence of
magnetic nanoparticle breaks the frequency and phase locking. Then
oscillation will disappear or diminish significantly.
FIG. 10 is a schematic block diagram of a magnetic oscillator
biosensor chip architecture. The biosensor chip consists of many
sub-arrays of the biosensors. Each sub-array can have one or more
than one fixed multilayer stacks (i.e., magnetic nano-oscillators)
as described above. In many embodiments, within a sub-array, the
fixed multilayer stacks are designed to have the same oscillation
frequency or oscillation frequencies very close to one another for
detection. Between sub-arrays, the oscillation frequencies are
sufficiently different in order to identify for the DNA spotters,
i.e., fixed multilayer stack sub-arrays. A frequency division
multiplexing (FDM) scheme is used to reduce the readout time. The
output signal is compared with reference frequency for signal
detection.
As shown in FIG. 10, the sub-arrays share the same control bus to
select the oscillators within a sub-array by Col_sel and Row_sel.
The sub-arrays in a row are frequency-division multiplexed to form
a channel, FDM Ch_A, FDM Ch_B, . . . or FDM Ch_N. A clock, CLK, is
used to generate the carrier frequencies for FDM. The output
signals from the FDM channels are then time-division multiplexed
(TDM) to further reduce the read-out time. The final output is then
compared to a reference to detect the signal. The final output can
also be digitized by an analog-digital converter (ADC) that is not
shown in the figure. Gain_ctl is used to adjust the gain of the FDM
channels. I_ctl is used for the current input to the chip.
FIG. 11 is a flow diagram 200 of an illustrative method for sensing
a target molecule with a magnetic oscillator biosensor. The method
includes passing a current through a fixed multilayer stack to
generate magnetization oscillation with the fixed multilayer stack
with the current at block 201. Then the magnetization oscillation
is detected at block 202. A magnetic complex is formed with a
target molecule and combined with a binding molecule that is bonded
to the sensor at block 203. Then at decision block 203, if the
oscillation frequency is altered then the target molecule is
detected at block 204, otherwise the target molecule is not
detected at block 205.
Thus, embodiments of the MAGNETIC OSCILLATOR BASED BIOSENSORS are
disclosed. The implementations described above and other
implementations are within the scope of the following claims. One
skilled in the art will appreciate that the present disclosure can
be practiced with embodiments other than those disclosed. The
disclosed embodiments are presented for purposes of illustration
and not limitation, and the present invention is limited only by
the claims that follow.
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